System and method for circuit compliance compensated pressure-regulated volume control in a patient respiratory ventilator

ABSTRACT

A system and a method for circuit compliance compensated pressure control in a patient respiratory ventilation system, having a pressure regulated feedback servo control loop, a pressure-regulated volume controller, and a patient volume observer. The patient volume observer is operative to estimate a patient volume, that is, the volume actually delivered to the patient by accounting for volume deviation or loss caused by patient circuit leakage and valve dynamics. Based on the difference between the estimated patient volume and a set tidal volume, the pressure-regulated volume controller is operative to generate and update a circuit compliance pressure compensation factor. The pressure regulated feedback servo control loop is operative to modulate the peak airway pressure based on the circuit compliance pressure compensation factor, so as to achieve the set tidal volume while maintaining a constant inspiratory time and a constant I:E ratio.

CROSS-REFERENCE TO RELATED APPLICATIONS

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STATEMENT RE: FEDERALLY SPONSORED RESEARCH/DEVELOPMENT

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BACKGROUND

The present invention relates in general to a system and a method for circuit compliance compensated pressure-regulated volume control in a patient respiratory ventilator, and more particularly, to a system and a method suitable for providing ventilation to patients at all sizes and ages by effectively and accurately estimating and compensating for the patient circuit compliance.

In order to deliver an accurate set tidal volume to a patient in a respiratory ventilation system, the patient circuit compliance has to be compensated. The compensation of patient circuit compliance is especially crucial for neonatal patients whose lung compliance can be as small as about one thirteenth of the circuit compliance. Without compensation for the circuit compliance, inaccurate volume delivery and inadequate flow will be delivered to the patient. Therefore, various designs and algorithms have been proposed to facilitate the patient circuit compliance compensation in the respiratory ventilation system. Currently, the setting or approaches in many of the circuit compliance compensation designs or algorithms cannot achieve precise volume delivery especially for neonatal patients without the risk of over delivering volume. Therefore, most of the ventilators available in the market do not allow for circuit compliance compensation designs applied to neonatal patients due to the stringent precision requirement on volume delivery. The burden of achieving accurate volume delivery is then left for the clinician.

Currently, algorithms that directly add an estimate of patient circuit volume to a set tidal volume are commonly used. An estimate of patient circuit volume is added to a set tidal volume by increasing the volume target, which ultimately increments the target peak airway pressure. The patient circuit volume is computed using the average peak airway pressure of previous mandatory breaths and an estimate of the patient circuit compliance, the patient circuit volume is thus continuously elevated breath after breath. Due to positive feedback of average peak airway pressure, when directly accounting for the circuit volume this algorithmic approach can establish a runaway (not converge) condition especially on neonatal patient sizes where the ratio of circuit compliance to patient (lung) compliance can be as high as 13:1. Moreover, this algorithm is not robust in cases where airway resistance is high due to effects such as gas compression which occurs as a result of positive feedback of peak airway pressure. Therefore, this algorithm is only effective on adults and some pediatrics patient sizes, and may not be responsive when changes in airway resistance and/lung compliance occur. A positive feedback approach to directly account for the circuit compliance/volume can thus have many adverse affects.

Therefore, there is a substantial need to develop a system and a method to provide circuit compliance compensated pressure regulated volume control in a patient respiratory ventilation system for the patients at all ages and sizes without causing any of the above adverse effects.

BRIEF SUMMARY

A system and a method for circuit compliance compensated pressure-regulated volume control in a patient respiratory ventilator clinically acceptable for patients at all sizes and ages are provided. The system and method as provided allow the patient to receive an accurate patient pressure while maintaining a constant ratio of inspiratory time versus expiratory time (I:E ratio) throughout volume delivery without causing gas trapping and auto PEEP. The existing on-board sensors are used for modulate the target airway pressure, so as to provide the set tidal volume to the patient. The operation of the system and the method are designed based on the governing physics of the patient/ventilator system, and the leakage of the patient circuit and actuator response & dynamics are taken into account during volume delivery. Therefore, the system and method are robust against changes in airway resistance and patient compliance.

A system for circuit compliance compensated pressure-regulated volume control in a patient respiratory ventilation system, having a pressure regulated feedback servo control loop, a pressure-regulated volume controller, and a patient volume observer. The patient volume observer is operative to estimate a patient volume, that is, the volume actually delivered to the patient by accounting volume deviation or loss caused by patient circuit leakage or actuator dynamics. Based on the difference between the estimated patient volume and a set tidal volume, the pressure-regulated volume controller is operative to generate and update a circuit compliance pressure compensation factor. The pressure regulated feedback servo control loop is operative to regulate the peak airway pressure of the patient based on the circuit compliance pressure compensation factor, so as to achieve the set tidal volume delivery while maintaining a constant inspiratory time and a constant I:E ratio.

In one embodiment, a method for circuit compliance compensated pressure-regulated volume control is provided. The method includes generating a circuit compliance pressure compensation factor based on a set tidal volume and an actual volume delivered to the patient. The actual volume delivered to the patient can be estimated by measurements from existing flow sensors and pressure transducer or measured directly from a flow sensor at the patient connection. The circuit compliance pressure compensation factor is updated by a dynamic gain which varies according to a ratio of volume distributed to the patient circuit and the volume flowing to the patient. The dynamically updated circuit compliance pressure compensation factor is then used to regulate a peak airway pressure. Based on the regulated peak airway pressure, the ventilator is operative to supply an appropriate net volume allowing the actual volume delivered to the patient to approach the set tidal volume within a few breaths.

A ventilation system that incorporating the above the system for circuit compliance compensated pressure regulated volume control is also provided. The ventilation system includes a ventilator for supplying inspiratory gas to the patient and re-circulating the expiratory gas exhaled from the patient and a patient circuit, preferably a Y-circuit, for providing the flow communication between the ventilator and the patient. Sensors and transducers are provided to measure the inspiratory flow, expiratory flow, patient flow, circuit pressure, and PEEP. By measurements of the above parameters, a circuit compliance compensation pressure factor can be generated and updated for regulating a peak airway pressure. The updated peak airway pressure is input to a servo control subsystem to control operation of the ventilator, such that the ventilator can deliver a net volume allowing the desired or predetermined set tidal volume to be delivered to the patient without prolonging the inspiratory time, so as to maintain a constant I:E ratio.

BRIEF DESCRIPTION OF THE DRAWINGS

These and other features and advantages of the various embodiments disclosed herein will be better understood with respect to the following description and drawings, in which like numbers refer to like parts throughout, and in which:

FIG. 1 illustrates a respiratory circuit diagram of a patient who is receiving machine ventilation;

FIG. 2 shows a graph of circuit compliance obtained from empirical data and an estimated circuit compliance approximated from the empirical data;

FIG. 3 illustrates a block diagram showing a ventilation system that incorporates a system for circuit compliance compensated pressure regulated volume control;

FIG. 4 shows a block diagram of the system for circuit compliance compensated pressure regulated volume control;

FIG. 5 illustrates a block diagram of a volume delivery controller of the system as shown in FIG. 4; and

FIG. 6 illustrates the regulated peak airway pressure for a plurality of breaths.

DETAILED DESCRIPTION

In an electric circuit, the electric current I flows from a high potential level to a low potential level. When the electric current flows through a passive circuit element such as a resistor, an inductor, a capacitor, or a load, a voltage drop ΔV is created across such element. When electric circuit comprises two or more of the similar circuit elements connected to each other in parallel, the total electric current is split into two smaller currents distributed flowing through the respective elements. The magnitude of the distributed currents depends on the characteristic values, such as the resistance, the conductance and the capacitance of the elements. In a patient respiratory circuit, the gas flow Q circulates from a high pressure level to a low pressure level in a way similar to the electric current I in the electric circuit; and the gas flow I flowing through an airway resistance causes a pressure drop ΔP similar to the voltage drop ΔV. FIG. 1 illustrates a circuit diagram of a patient respiratory circuit. As shown, the patient respiratory circuit comprises a patient circuit for circulating gas between a ventilator and a patient. The ventilator is operative to provide an inspiratory gas flow Q_(INSP) to the patient and receive an expiratory gas flow Q_(EXP) exhaled from the patient through the patient circuit. Ideally, 100% of the net flow Q_(NET) delivered from the ventilator, that is, the flow differential between the inspiratory flow Q_(INSP) and the expiratory flow Q_(Exp), is to be delivered to the patient, such that the set tidal volume can be delivered to the patient. However, in real practice, the volume loss within the patient circuit is inevitable due to the distensibility at least partially attributed tot eh circuit compliance C_(T) thereof. As shown, the circuit compliance C_(T) that behaves similarly to a capacitor in an electric current is in parallel flow communication with the lung compliance C_(L) in the patient respiratory circuit.

By measuring the inspiratory flow Q_(INSP) and the expiratory flow Q_(EXP), the machine delivered net volume V_(NET) can be computed by integrating by the net gas Q_(NET), that is, the flow differential between the inspiratory flow Q_(INSP) and the expiratory flow Q_(EXP). Without the circuit compliance compensation, the machine delivered net volume V_(NET) is equivalent to the set tidal volume delivered by the ventilator. However, as a portion of the net flow Q_(NET) is offset by the circuit compliance C_(T), the volume actually delivered to the patient's lung is smaller than the set tidal volume. That is, the patient cannot receive the set tidal volume as desired. As the circuit compliance C_(T) is defined as a ratio of the volume offset by the patient circuit to the pressure across the patient circuit, the volume offset by the circuit compliance is thus proportional to the circuit compliance C_(T). Therefore, when the circuit compliance C_(T) is much larger than the lung compliance C_(L), a majority part of the net flow Q_(NET) will be distributed to the patient circuit instead of being supplied to the patient's lung.

In the embodiment as shown in FIG. 1, the ground level that the patient circuit connects to is set at the positive end expiratory pressure (PEEP). Therefore, the pressure drop across the patient circuit is the pressure differential ΔP between the measured pressure P_(y) and PEEP. Typically, an airway resistance R_(L) exists in the patient's airway, such that the pressure applied to the patient's lung will be offset by a factor of Q_(L) ²R_(L). The pressure at the patient circuit P_(Y) and the lung pressure P_(L) can thus be expressed by the following equation: P _(Y) =P _(L) +Q _(L) ² R _(L)  (1). By definition, the circuit compliance C_(T) and the lung compliance C_(L) can be expressed as:

$\begin{matrix} {{C_{L} = \frac{V_{TID}}{P_{L} - {PEEP}}};{and}} & (2) \\ {{C_{T} = \frac{V_{CC}}{P_{Y} - {PEEP}}},} & (3) \end{matrix}$ where V_(TID) is equivalent to V_(L), which is the actual gas volume delivered to the lung of the patient, and V_(CC) is the gas volume offset by the circuit compliance. The gas volumes V_(TID) and V_(CC) can be derived by integrating the gas flow Q_(T) and Q_(L) flowing through the patient circuit and the patient's lung L. Therefore, the sum of the gas volumes V_(CC) and V_(L) is equal to the net gas volume V_(NET) as expressed by Equation (4), which can be integrated from the net gas flow Q_(NET). V _(NET) =V _(CC) +V _(TID)  (4). From Equations (3) and (4), an estimate of patient volume can be expressed as: {circumflex over (V)} _(TID) =V _(NET) −V _(CC) =V _(NET) −C _(T)(P _(Y)−PEEP)  (5). From Equations (1) and (2),

$\begin{matrix} {{P_{Y} - {PEEP}} = {\frac{V_{TID}}{C_{L}} + {Q_{L}^{2}{R_{L}.}}}} & (6) \end{matrix}$ From Equations (5) and (6), an estimate of the net volume that the ventilator needs to deliver is:

$\begin{matrix} \begin{matrix} {V_{NET} = {V_{TID} + {{C_{T}\left( {P_{Y} - {PEEP}} \right)}\mspace{14mu}{or}}}} \\ {{{V_{NET} = {V_{TID} + {C_{T}\left( {\frac{V_{TID}}{C_{L}} + {Q_{L}^{2} \cdot R_{L}}} \right)}}};{{and}\mspace{14mu}{therefore}}},} \\ {{\hat{V}}_{NET} = {{\left( {1 + \frac{C_{T}}{C_{L}}} \right)V_{TID}} + {C_{T} \cdot Q_{L}^{2} \cdot {R_{L}.}}}} \end{matrix} & (7) \end{matrix}$ From Equation (7), the machine delivered volume V_(NET) can be computed if the lung compliance C_(L), the circuit compliance C_(T), the airway resistance R_(L), the desired patient flow Q_(L), and the desired patient flow V_(TID) are known. It will be appreciated that, as the volume parameters in Equation (7) are integrations of the corresponding gas flows, the pressure parameter P_(Y) typically indicates the peak pressure at the patient circuit.

In Equation (7), since the lung compliance C_(L) and the airway resistance R_(L) can vary with time or condition, it would be very difficult to accurately determine the appropriate machine delivered volume as desired on a real-time basis. Therefore, as provided in this embodiment, the system and method for circuit compliance compensated pressure control estimate the patient volume and the patient circuit volume using the existing sensors in the ventilator. For example, the actual inspiratory gas flow Q_(INSP) and the expiratory gas flow Q_(EXP) are measured by the existing sensors of the ventilation machine used by the patient, and the net machine delivered flow Q_(NET) can be derived from the difference thereof. Alternatively, the machine delivered net flow Q_(NET) can be obtained from direct measurement by the sensor installed at the patient circuit. In such manner, various volume variables can be obtained based on the true inhalation and exhalation of the patient, and the set peak airway pressure can be regulated based on the volume variables.

By definition, the positive end expiratory pressure PEEP is the pressure P_(Y) measured at the end of the expiratory phase. Therefore, before the patient is receiving the machine ventilation, the ground pressure level of the patient circuit is zero or other preset values. The circuit compliance C_(T) can be predetermined by providing known volumes to the patient circuit and measuring the responsive circuit pressure at each specific volume as supplied. The circuit compliance C_(T) for a specific patient circuit can thus be expressed by an empirical relationship between the circuit volume V_(CC) and the circuit pressure ΔP_(Y) (=P_(Y)). When the patient circuit is applied to circulate gas between the ventilator and the patient to construct the patient respiratory circuit as shown in FIG. 1, one can then derive the circuit volume V_(CC) from the empirical relationship by measuring the circuit pressure ΔP_(Y) (=P_(Y)−PEEP). In this embodiment, the pressure P_(Y) is defined as the pressure measured at the expiratory limb of the patient circuit during the inspiratory phase, that is, P_(Y)=P_(EXP) during I-phase; or P_(Y) is the average pressure between P_(EXP) and the pressure measured at the inspiratory limb of the patient circuit during the expiratory phase P_(INSP), that is, P_(Y)=(P_(INSP)+P_(EXP))/2 during E-phase.

FIG. 2 shows the relationship between the circuit volume V_(CC) and the pressure differential ΔP_(Y) obtained from empirical data. As shown, the empirical data show a nearly linear relationship between the circuit volume V_(CC) and the differential circuit pressure ΔP_(Y). Therefore, a linear line with a slope CKT_CMP_(SLP) that reflects the circuit compliance C_(T) can be drawn from the graph, and the circuit volume V_(CC) can be presented by the equation as: {circumflex over (V)} _(CC) =CKT _(—) CMP _(SLP)·(P _(Y)−PEEP)+CKT _(—) CMP _(INT)  (8), where CKT_CMP_(INT) is the intercept with the V_(CC) axis. It will be appreciated that, depending on specific setup parameters and conditions of the patient, the relationship between the circuit V_(CC) and the circuit pressure ΔP_(Y) may vary from Equation (8). For example, a nonlinear behavior may be observed from the empirical data. Further, a lookup table listing the circuit volume for each responsive circuit pressure can also be used for one to estimate the circuit volume V_(CC).

When the circuit volume of the patient circuit is obtained, the tidal volume actually delivered to the patient can be estimated from Equation (4), that is, {circumflex over (V)} _(TID) =V _(NET) −{circumflex over (V)} _(CC)  (9) As mentioned above, the net volume delivered by the machine V_(NET) can be derived by integrating the net flow delivered by the machine Q_(NET), that is, the difference between the inspiratory and expiratory gas flows Q_(INSP) and Q_(EXP). That is, V _(NET)=∫_(Start of I−phase) ^(Q) ^(NET) ^(crosses 0)(Q _(INSP) −Q _(Exp))dt  (10). In this embodiment, the circuit volume V_(CC) will not be updated until the differential gas flow, that is, the net gas flow Q_(NET) (=Q_(INSP)−Q_(EXP)), crosses zero; and therefore, the calculation or computation of the net machine delivered volume V_(NET) is integrated over the differential gas flow Q_(NET) from the start of the inspiratory phase to the time when the net flow Q_(NET) crosses 0. In the case that the net flow Q_(NET) crosses 0 before the inspiratory phase is complete, the circuit volume V_(CC) and the tidal volume V_(TID) are estimated.

FIG. 3 illustrates a patient ventilation circuit or system incorporating the system for circuit compliance compensated pressure-regulated volume control discussed above. As shown in FIG. 3, the ventilation system includes a ventilator 10, a patient circuit 20 for circulating the inspiratory gas and the expiratory gas between the ventilator 10 and a patient, the system for circuit compliance compensated pressure-regulated volume control 30, and a servo control subsystem 40 for controlling operations of the ventilator 10. The ventilator 10 typically includes a user interface such as a monitor 12 for displaying various conditions and parameters of the patient and the ventilation system, and an input device (not shown) allowing the operator or user to input the required settings and parameters. The input device may include switches, buttons or any adjusting devices built on the front panel of the monitor or other devices including keyboard, mouse or remote controls operative to provide data or information input by the user or operator to a processor (not shown) of the ventilator 10. Alternatively, the monitor 12 may be in the form of a touch screen in which both the display and input device are integrated. Based on the input data or information, the processor is operative to control the ventilator 10 for performing the desired operations. The ventilator 10 further includes an inspiratory port 14 and an expiratory port 16 through which the inspiratory gas and the expiratory gas are supplied to and received from the patient through the patient circuit. An inhalation flow control valve or orifice is typically installed at the inspiratory port 14 for controlling the inspiratory flow Q_(INSP), and an exhalation valve is preferably installed at the expiratory port for controlling the open/close condition of the expiratory port 16. In this embodiment, inspiratory and expiratory flow sensors 11 and 13 are installed at the inspiratory and expiratory ports 14 and 16 for measuring the inspiratory Q_(INSP) and expiratory flow Q_(EXP), respectively. In addition, an inspiratory pressure transducer 15 and an expiratory pressure transducer 17 may also be installed to measure the inspiratory and expiratory pressure P_(INSP)and P_(EXP), respectively.

As shown, the patient circuit 20, such as a Y circuit, is used to connect the ventilator 10 to the patient, so as to construct the respiratory circuit for circulating gas between the ventilator 10 and the patient. The Y circuit 20 includes an inspiratory limb 22 with one end connected to the inspiratory port 14 and an expiratory limb 24 with one end connected to the expiratory port 16 of the ventilator 10. The other ends of the inspiratory limb 22 and the expiratory limb 24 merge with each other at one end of a patient piece 26, of which the other end is applied to the patient. Other accessories or component devices such as filters may also be installed in various parts of the Y circuit 20. For example, a flow sensor 28 is preferably installed at the patient piece 26 to directly measure the patient flow Q_(Y) delivered to the patient. It will be appreciated that the inspiratory and expiratory flow sensors 11 and 13 may also be installed on the inspiratory limb 22 and the expiratory limb 24, respectively. Preferably, the measurable process variables, including the inspiratory flow Q_(INSP), the expiratory flow Q_(EXP), the inspiratory pressure P_(INSP), the expiratory pressure P_(EXP), and PEEP are measured according to a predetermined sampling rate. For example, in one embodiment, these process variables are sampled every 2 msce. The ventilator 10 may further comprises a sensor processor 18 operative to process the measured process variables or parameters, including Q_(INSP), Q_(EXP), P_(INSP), P_(EXP) and other sensor readings such as Q_(Y) before outputting them to the circuit compliance compensated pressure-regulated volume control system 30. The sensor processor 18 may be configured as an individual sensor in communication with the sensors 11, 13, 15, 17 and 28 and the circuit compliance compensated pressure-regulated volume control system 30. Alternatively, the sensor processor 18 may be integrated into the above-mentioned processor of the ventilator 10 that control the operations of the ventilator 10.

Referring to FIGS. 3 and 4, the system for circuit compliance compensated pressure-regulated volume control 30 includes a circuit compliance estimator 31, a patient circuit volume estimator 32, a patient volume observer 33, a pressure-regulated volume controller 34, and an initial target pressure calculator 35. As discussed above, the circuit compliance C_(T) of the patient circuit 20 can be estimated by measuring the pressure differential ΔP_(Y) at various circuit volumes V_(CC). In this embodiment, the circuit compliance estimator 31 is operative to provide a relationship between the circuit volume V_(CC) and the pressure differential ΔP_(Y) based on empirical data. The relationship may be in the form of a mathematical equation of V_(CC) and ΔP_(Y) or a lookup table reflecting the corresponding circuit volumes V_(CC) for a specific circuit pressure ΔP_(Y). When the empirical data show a linear relationship as expressed by Equation (8), the slope CKT_CMP_(SLP) and the intercept CKT_CMP_(INT) are estimated by the circuit compliance estimator. The slope CKT_CMP_(SLP) and the intercept CKT_CMP_(INT) of the circuit compliance estimator 31 are then output to the patient circuit volume estimator 32. The circuit volume estimator 32 is also connected to the ventilator 10 for receiving the Y circuit pressure P_(Y) and the PEEP measured by the pressure transducers 17 (or 15 and 17), such that the pressure differential ΔP_(Y) can be computed. Based on ΔP_(Y), the slope CKT_CMP_(SLP) and the intercept CKT_CMP_(INP), the patient circuit volume V_(CC) can be estimated by Equation (8) and denoted as VOL_(CKT) _(—) _(EST) output to the patient volume observer 33.

The patient volume observer 33 is operative to receive the measured net machine delivered volume VOL_(NET), that is, the machine delivered net volume derived by integrating the net flow Q_(NET), and the estimated circuit volume VOL_(CKT) _(—) _(EST) estimated by the circuit volume estimator 32. By subtracting the estimated circuit volume VOL_(CKT) _(—) _(EST) from the measured machine delivered net volume VOL_(NET) derived by integrating the net flow Q_(NET), the true volume VOL_(TID) delivered to the patient, that is, the estimated patient volume VOL_(TID) _(—) _(EST) can be obtained by the patient volume observer (virtual sensor) 33. Preferably, the estimated circuit volume VOL_(CKT) _(—) _(EST) and the estimated patient volume VOL_(TID) _(—) _(EST) are updated according to the timing when the net flow Q_(NET) crosses zero instead of the timing when the machine breaths cycles from inspiratory phase to expiratory phase. The update timing for volume variables are discussed in details as follows.

Preferably, when a patient circuit disconnect is detected or when any type of circuit integrity alarm is activated, the volume variables will not be updated until the patient circuit is reconnected or the alarm is off. That is, the measured machine delivered net volume VOL_(NET), the estimated patient volume VOL_(TID) _(—) _(EST) and the estimated circuit volume VOL_(CKT) _(—) _(EST) freeze at the previously computed values as: VOL_(NET) _(K) =VOL_(NET) _(K−1) ; VOL_(CKT) _(—) _(EST) _(K) =VOL_(CKT) _(—) _(EST) _(K−1) ; and VOL_(TID) _(—) _(EST) _(K) =VOL_(TID) _(—) _(EST) _(K−1)   (11), where K is an index for indicating the currently computed variables and K−1 for indicating the previously computed variables. The sampling intervals can be variable according to specific conditions, requirements, or setup parameters.

When the flow sensor 28 is installed at the patient piece 26 of the patient circuit 20, the patient flow Q_(Y) can be measured, and a measured patient volume VOL_(TID) _(—Y) can be computed to facilitate volume limit of the pressure regulated volume delivery controller 34, so as to prevent an excessive circuit compliance pressure compensation factor PRS_(TID) _(—) _(CTL) from being generated and output there from. The measured patient volume VOL_(TID) _(—) _(Y) can also be used to replace the estimated patient volume VOL_(TID) _(—) _(EST) for calculating the circuit compliance pressure compensation factor PRS_(TID) _(—) _(CTL). The application of the measured patient volume VOL_(TID) _(—) _(Y) will be discussed in details later in the specification. In addition to the measured patient volume VOL_(TID) _(—) _(Y), another volume variable, that is, the inspiratory volume VOL_(INSP) can also be obtained by integrating the inspiratory flow Q_(INSP). Similarly to the volume variables presented in Equation (11), computation of these two volume variables are frozen at the previously computed values whenever the patient circuit disconnect is detected or any circuit integrity alarm is activated as: VOL_(TID) _(—) _(Y) _(K) =VOL_(TID) _(—) _(Y) _(K−1) ; and VOL_(INSP) _(K) =VOL_(INSP) _(K−1) .  (11-1) Preferably, at the start of every inspiratory phase, or whenever any user set value of the ventilator 10 varies, the measured machine delivered net volume VOL_(NET), the measured patient volume VOL_(TID) _(—) _(Y), and the inspiratory volume VOL_(INSP) are reset to an initial value (0 in this embodiment) and updated from the initial value every sampling interval (2 msec, for example) as: VOL_(NET) _(K−1) =0,VOL_(NET) _(K) =(Q _(NET) _(K) /60)*0.002 VOL_(TID) _(—) _(Y) _(K−1) =0,VOL_(TID—) _(Y) _(K) =(Q _(TID) _(—) _(Y) _(K) /60)*0.002 VOL_(INSP) _(K−1) =0,VOL_(INSP) _(K) =(Q _(INSP) _(K) /60)*0.002  (12)

During the inspiratory phase, the net flow Q_(NET), the patient delivered flow Q_(Y), and the inspiratory flow Q_(INSP) are continuously monitored. When the inspiratory phase has started for at least a predetermined period of time such as 50 milliseconds and the net flow Q_(NET) crossed zero, that is, when Q_(NET) _(K) <0 and Q_(NET) _(K−1) >0, a zero-crossing net flow is detected and flagged, while the net machine delivered VOL_(NET), the measured patient volumes VOL_(TID) _(—) _(Y), and the inspiratory volume VOL_(INSP) are continuously updated as: VOL_(NET) _(K) =VOL_(NET) _(K−1) +(Q _(NET) _(K) /60)*0.002,VOL_(NET) _(K) =max(VOL_(NET) _(K) , 0) VOL_(TID) _(—) _(Y) _(K) =VOL_(TID) _(—) _(Y) _(K−1) +(Q _(TID) _(—) _(Y) _(K) /60)*0.002, VOL_(TID) _(k) =max(VOL_(TID) _(—) _(y) _(k) ,0). VOL_(INSP) _(K) =VOL_(INSP) _(K−1) +(Q _(INSP) _(K) /60)*0.002  (13).

If the net flow Q_(NET) has been detected to cross zero during the inspiratory phase, the estimated circuit volume VOL_(CKT) _(—) _(EST) and the estimated patient volume VOL_(TID) _(—) _(EST) are updated at the start of the expiratory phase following the inspiratory phase as: {circumflex over (V)}OL_(CKT) _(—) _(EST) _(K) =CKT _(—) CMP _(SLP)·(P _(Y) _(K) −PEEP_(K))+CKT _(—) CMP _(INT) {circumflex over (V)}OL_(TID) _(—) _(EST) _(K) =VOL_(NET) _(K) −{circumflex over (V)}OL_(CKT) _(—) _(EST) _(K) {circumflex over (V)}OL_(TID) _(—) _(EST) _(K) =max({circumflex over (V)}OL_(TID) _(—) _(EST) _(K) ,0)  (14); and the machine delivered net volume VOL_(NET) and the measured patient volume VOL_(TID) _(—) _(Y) are reset to the initial setup values and updated from the initial setup values as: VOL_(NET) _(K−1) =0,VOL_(NET) _(K) =(Q _(NET) _(K) /60)*0.002,VOL_(NET) _(K) =min(VOL_(NET) _(K) ,0) VOL_(TID) _(—) _(Y) _(K) =0, VOL_(TID) _(—) _(Y) _(K) =(Q _(TID) _(—) _(Y) _(K) /60)*0.002, VOL_(TID) _(—) _(Y) _(K) =min(VOL_(TID) _(—) _(Y) _(K) ,0)  (15).

Under the condition that the net flow Q_(NET) does not cross zero during the inspiratory phase, the machine delivered net volume VOL_(NET) and the measured patient volume VOL_(TID) _(—) _(Y) will not be reset at the start of the expiratory phase. That is, the machine delivered net volume VOL_(NET) and the measured patient volume VOL_(TID) _(—) _(Y) are continuously updated during the expiratory phase as Equation (13).

Following the condition that the net flow Q_(NET) does not cross zero during the inspiratory phase, when the zero-crossing net flow Q_(NET) is detected within a predetermined period of time such as 100 msec after the machine breath has cycled to the expiratory phase (that is, when TIME_(EXP)<100 msec, Q_(NET) _(K) <0 and Q_(NET) _(K−1) >0); or alternatively, when the expiratory phase has lasted over the predetermined period (100 msce) before the zero-crossing net flow Q_(NET) is detected (that is, TIME_(EXP)>100 msec and Q_(NET) _(K) >0), the estimated circuit volume VOL_(CKT) _(—) _(EST) and the estimated patient volume VOL_(TID) _(—) _(EST) are updated according to Equation (14), while the measured machine delivered net volume VOL_(NET) and the measured patient volume VOL_(TID) _(—) _(Y) are reset and updated as: VOL_(NET) _(K−1) =0,VOL_(NET) _(K) =(Q _(NET) _(K) /60)*0.002,VOL_(NET) _(K) =min(VOL_(NET) _(K) ,0) VOL_(TID) _(—) _(Y) _(K) =0,VOL_(TID) _(—) _(Y) _(K) =(Q _(TID) _(K) /60)*0.002,VOL_(TID) _(—) _(Y) _(K) =min(VOL_(TID) _(—) _(y) _(k) ,0)  (17). In this embodiment, the measured machine delivered net volume VOL_(NET) and the measured patient volume VOL_(TID) _(—) _(Y) are reset according to the timing when the net flow Q_(NET) crosses zero instead of the phase transition of machine breath. This allows the calculations of the estimated circuit volume VOL_(CKT) _(—) _(EST) and the estimated patient volume VOL_(TID) _(—) _(EST) to be synchronized with true patient inhalation and exhalation. Thereby, a more accurate patient volume can be computed. The estimated patient volume is thus updated according to the timing when the net flow Q_(NET) crosses zero, such that all of the machine delivered net volume VOL_(NET) can be accounted even when the patient breath and the machine breath are out of phase, that is, when the net flow Q_(NET) does not cross zero at the time the machine breath is cycling to the expiratory phase.

At the beginning of every inspiratory phase, the estimated patient volume VOL_(TID) _(—) _(EST) is subtracted from a set tidal volume VOL_(TID) _(—) _(SET) to obtain a volume error VOL_(TID) _(—) _(ERR) that reflects the error between the set tidal volume and the estimated tidal volume actually delivered to the patient. The volume error VOL_(TID) _(—) _(ERR) can thus be expressed and computed from the following equation as: VOL_(TID) _(—) _(ERR) _(K) =VOL_(TID) _(—) _(SET) _(K) −{circumflex over (V)}OL_(TID) _(—) _(EST) _(K−1) ,  (18) The volume error VOL_(TID) _(—) _(ERR) can thus be used to compute an estimated circuit compliance pressure compensation factor PRS_(TID) _(—) _(CTL) by the pressure-regulated volume controller 34, so as to modulate the patient airway peak pressure P_(SET) and ensure the set tidal volume delivered to the patient. At the beginning of the computation, the initial output for the regulated-pressure volume controller is input to the pressure-regulated volume controller 34, that is, the estimated circuit compliance pressure compensation factor PRS_(TID) _(—) _(CTL) is initialized as: PRS_(TID) _(—) _(CTL)=INI_(—) CKT _(—) PRS  (19). The estimated circuit compliance pressure compensation factor PRS_(TID) _(—) _(CTL) is reset to the initial value INI_CKT_PRS whenever the user setting of the ventilator 10 are altered. That is, any time when a new set of parameters is input to the system, the estimated circuit compliance pressure compensation factor PRS_(TID) _(—) _(CTL) will be reset to the initial value INI_CKT_PRS and updated for every breath.

In the embodiment as shown in FIG. 5, the pressure-regulated volume controller 34 further comprises an error percentage converter 341, a gain scheduler 342, and a pressure integrator 345 for generating the circuit compliance pressure compensation volume factor PRS_(TID) _(—) _(CTL) for each breath. The error percentage converter 341 is used to provide a volume error percentage defined by a ratio of an absolute value of the volume error VOL_(TID) _(—) _(ERR) to the set tidal volume VOL_(TID) _(—) _(SET) as:

$\begin{matrix} {{VOL}_{{{PCT}\_{ERR}}_{K}} = {\frac{{VOL}_{{{TID}\_{ERR}}_{K}}}{{VOL}_{{{TID}\_{SET}}_{K}}} \times 100.}} & (20) \end{matrix}$

The error percentage VOL_(PCT) _(—) _(ERR) provides a useful indication of the ratio between the circuit compliance C_(T) to the lung compliance C_(L) of the patient. More specifically, when error percentage VOL_(PCT) _(—) _(ERR) is large, it indicates that a majority of the measured delivered net volume VOL_(NET) is distributed to the patient circuit 20 instead of being supplied to the patient's lung. Under such circumstance, a larger amount of volume may be required to compensate for the circuit compliance C_(T) in order to estimate a correct machine delivered net volume which renders the volume actually delivered to the patient to the set tidal volume VOL_(TID) _(—) _(SET). On the other hand, when the error percentage VOL_(PCT) _(—) _(ERR) is small, it indicates the volume actually delivered to the patient is close to the set tidal volume as desired and set up. Therefore, only a small amount of volume is required to compensate for the circuit compliance C_(T) of the patient circuit 20. As it has been discussed above, the lung compliance C_(L) is defined as the ratio of the volume delivered to the lung to the pressure applied to the lung of the patient (P=V_(TID)/C_(L)), the pressure is proportional to the volume delivered to the patient. Therefore, the volume error VOL_(TID) _(—) _(ERR) also reflects the pressure error between the set peak airway pressure and the actually peak airway pressure applied to the patient. The pressure-regulated volume controller 34 can thus use the gain scheduler 342 to provide a gain K_(PTID) according to the error percentage VOL_(PCT) _(—) _(ERR). The gain K_(PTID) is then input to a multiplier 343 for dynamically weighting and converting the error volume VOL_(PCT) _(—) _(ERR) into a pressure weight, or namely, a pressure correction BRTH_(PTID) _(—) _(CTL). Preferably, the gain K_(PTID) is presented in the unit of cmH2O/ml or another other pressure unit per unit volume. With the integrator 345 as shown in FIG. 5, the circuit compliance pressure compensation factor PRS_(TID) _(—) _(CTL), that is, the circuit compliance pressure compensation factor PRS_(TID) _(—) _(CTL) as computed in the previous breath is updated by adding the pressure correction BRTH_(PTID) _(—) _(CTL) thereto as: PRS _(TID) _(—) _(CTL) _(K) =BRTH _(PTID) _(—) _(CTL) _(K) +PRS _(TID) _(—) _(CTL) _(K−1)   (21) As shown, at the beginning of the computation, that is, for the first breath when the computation starts, the value of the circuit compliance pressure compensation factor PRS_(TID) _(—) _(CTL) is initialized as INI_CKT_PRS and input to the integrator 345 and continuously updated breath after breath by the pressure correction BRTH_(PTID) _(—) _(CTL) obtained from the multiplier 343.

Preferably but optionally, the pressure-regulated volume controller 34 may further comprise a breath pressure correction limiter 344 and a pressure restrictor 346 to rate limit the amount of pressure correction BRTH_(PTID) _(—) _(CTL) for the current breath and to prevent the updated circuit compliance pressure compensation factor PRS_(TID) _(—) _(CTL) exceeding allowable ranges from being output. The allowable range for the pressure correction BRTH_(PTID) _(—) _(CTL) includes a predetermined maximum value MAX_(PRS) _(—) _(RATE) and a predetermined minimum value MIN_(PRS) _(—) _(RATE). In this embodiment, a symmetric upper and lower limit is selected for the allowable range of the pressure correction BRTH_(PTID) _(—) _(CTL). That is, the minimum value MIN_(PRS) _(—) _(RATE) is set as the negative maximum value as −MAX_(PRS) _(—) _(RATE), such that the pressure correction BRTH_(PTID) _(—) _(CTL) output from the breath pressure correction limiter 344 will be limited as: BRTH _(PTID) _(—) _(CTL) _(K) =max(K _(PTID)*VOL_(TID) _(—) _(ERR) _(K) , −MAX_(PRS) _(—) _(RATE)) BRTH _(PTID) _(—) _(CTL) _(K) =min(BRTH _(PTID) _(—) _(CTL) _(K) , MAX_(PRS) _(—) _(RATE))  (22) Referring in FIGS. 4 and 6, the circuit compliance compensated pressure-regulated volume control system 30 further comprises an initial target pressure calculator 35 to calculate the initial peak airway pressure P_(SET) _(—) _(INI) defined as an average of a predetermined maximum value PRS_(MAX) and a predetermined minimum value PRS_(MIN) for the target peak airway pressure P_(SET) as: P _(SET) _(—) _(INI)=(PRS _(MAX) +PRS _(MIN))/2  (23) As shown, the initial value of the circuit compliance pressure compensation factor PRS_(TID) _(—) _(CTL) is preset as INI_CKT_PRS, and the updated circuit compliance pressure compensation factor PRS_(TID) _(—) _(CTL) is limited between MAX_(PRS) _(—) _(TID) and −MAX_(PRS) _(—) _(TID) by the pressure restrictor 346 as: PRS _(TID) _(—) _(CTL)=min(MAX_(PRS) _(—) _(TID) , PRS _(TID) _(—) _(CTL)) PRS _(TID) _(—) _(CTL)=max(−MAX_(PRS) _(—) _(TID) , PRS _(TID) _(—) _(CTL)) MAX_(PRS) _(—) _(TID)=(PRS _(MAX) −PRS _(MIN))/2  (24). Thereby, the target peak airway pressure P_(SET) can also be limited between PRS_(MAX) and PRS_(MIN) to avoid excessive adjustment that will cause adverse or harmful effect to the patient.

As discussed above, the measured patient volume VOL_(TID) _(—) _(Y) can be used as a volume limit reference to prevent the pressure-regulated volume controller 34 from excessively generating the circuit compliance pressure compensation factor PRS_(TID) _(—) _(CTL). To this extent, the system for circuit compliance compensated pressure control 30 further comprises a volume limiter 37 to receive the measured patient volume VOL_(TID) _(—) _(Y) and compare the measured patient VOL_(TID) _(—) _(Y) to the set tidal volume VOL_(TID) _(—) _(SET). Before the measured patient volume VOL_(TID) _(—) _(Y) reaches the set tidal volume VOL_(TID) _(—) _(SET), that is, when VOL_(TID) _(—) _(Y)<VOL_(TID) _(—) _(SET), the pressure-regulated volume controller 34 operates normally to generate the circuit compliance pressure compensation factor PRS_(TID) _(—) _(CTL) according to Equation (21). Once the measured patient volume VOL_(TID) _(—) _(Y) reaches the set tidal volume VOL_(TID) _(—) _(SET), the circuit compliance pressure compensation factor PRS_(TID) _(—) _(CTL) is frozen at the value computed in the previous breath as: PRS _(TID) _(—) _(CTL) _(K) =PRS _(TID) _(—) _(CTL) _(K−1)   (25). Effectively, the volume limiter 37 is operative to switch on or activate operation of the pressure-regulated volume controller 34 when the measured patient volume VOL_(TID) _(—) _(Y) is smaller than the set tidal volume VOL_(TID) _(—) _(SET), and switch off or inactivate operation of the pressure-regulated volume controller 34 when the measured patient volume VOL_(TID) _(—) _(Y) is equal to or larger than the set tidal volume VOL_(TID) _(—) _(SET). It will be appreciated that when the actual measured patient volume VOL_(TID) _(—) _(Y) is used for feedback, a volume limiter 37 will not be needed since the volume error VOL_(TID) _(—) _(ERR) would be 0 when actual measured patient volume VOL_(TID) _(—) _(Y) reaches the set tidal volume VOL_(TID) _(—) _(SET); and consequently, the circuit compliance pressure compensation factor PRS_(TID) _(—) _(CLT) updated by the weighted volume error VOL_(TID) _(—) _(CTL) will remain the same as that computed in the previous breath expressed as Equation (25).

Referring to FIG. 4, the circuit compliance pressure compensation factor PRS_(TID) _(—) _(CTL) generated and output by the pressure-regulated volume controller 34 is then input to an adder/subtractor 303, in which the peak airway pressure P_(SET) _(—) _(INI) is input and added to the circuit compliance pressure compensation factor PRS_(TID) _(—) _(CTL) as: P _(SET) _(K) =PRS _(TID) _(—) _(CTL) _(K) +P _(SET) _(—) _(INI) _(K)   (26). where P_(SET) _(—) _(INI)=(PRS_(MAX)+PRS_(MIN))/2 in this embodiment.

The estimated peak airway pressure P_(SET) is then input to the ventilator 10 and patient circuit 20 via the servo control subsystem 40, such that the ventilator 10 can provide a circuit compliance compensated peak airway pressure P_(SET) applied to the patient, so as to ensure the ventilator 10 delivering sufficient volume which allows the set tidal volume VOL_(TID) _(—) _(SET) delivered to the patient as desired. As shown in FIG. 4, the servo control subsystem 40, upon receiving the updated peak airway pressure P_(SET), is operative to output a flow control signal FCV_(D/A) to the ventilator 10 for controlling the flow control valve at the inspiratory port 14. Thereby, the inspiratory flow Q_(INSP) output from the inspiratory port 14 can be adjusted to provide the updated peak airway pressure P_(SET). The servo control subsystem 40 is further operative to output an exhalation valve control EV_(D/A) to control the open/close timing or status of the expiratory port 16 of the ventilator 10 in order to control exhalation of the patient.

Further referring to FIG. 4, in the pressure control mode, the machine breath is controlled to cycle from an inspiratory phase to an expiratory phase preset at T_(INSP) _(—) _(SET). Therefore, when the inspiratory phase reaches the preset phase transition time T_(INSP) _(—) _(SET), the machine breath is cycling from the inspiratory phase to the expiratory phase, and depending on the timing when the net flow Q_(NET) crosses zero, the estimated circuit volume VOL_(CKT) _(—) _(EST) and the estimated patient volume VOL_(TID) _(—) _(EST) are updated. The transition of phase is detected by a phase detector 36 as shown in FIG. 4, for example.

Further referring to FIG. 4, the system of circuit compliance compensated pressure control 30 further comprises a plurality of adders/subtractors 301, 302, and 303. As shown, the adder/subtractor 301 is operative to receive the inspiratory flow Q_(INSP) and the expiratory flow Q_(EXP), so as to calculate and provide the measured machine delivered net volume VOL_(NET) to the patient volume observer 32. The adder/subtractor 302 has two inputs to receive the set tidal volume VOL_(TID) _(—) _(SET) and the estimated patient volume VOL_(TID) _(—) _(EST) from the patient volume observer 32. Thereby, the volume error VOL_(TID) _(—) _(ERR) between the set tidal volume VOL_(TID) _(—) _(SET) and the estimated patient volume VOL_(TID) _(—) _(EST), that is, the error between the desired tidal volume and actual tidal volume delivered to the patient can be estimated. The adder/subtractor 303 adds the circuit compliance pressure compensation factor PRS_(TID) _(—) _(CTL) to the set peak airway pressure P_(SET) _(—) _(INI) to obtain a target peak airway pressure P_(SET). The output of the adder/subtractor 303 is connected to the servo control subsystem 40, from which the ventilator 10 is informed with the target peak airway pressure P_(SET) to be supplied to the patient. The circuit compliance compensated pressure regulated volume control system 30 further includes integrators 312 and 313 to compute the measured machine delivered volume VOL_(NET) and the measured patient volume VOL_(TID) _(—) _(Y) when the Y circuit flow Q_(Y) is measured, respectively.

As discussed above, the measured patient volume VOL_(TID) _(—) _(Y) can be used to as a volume limit reference in a volume limiter 37 for controlling operation of the pressure-regulated volume controller 34. Preferably, the volume limit is reset at the beginning of every inspiratory phase and cleared whenever the Y flow sensor is not in use. In certain circumstances, the measured patient volume VOL_(TID) _(—) _(Y) can be used to replace the estimated patient volume VOL_(TID) _(—) _(EST) for computing the circuit compliance pressure compensation factor PRS_(TID) _(—) _(CTL). Such application can be implemented by installing a switch 38 which selectively connects the output of integrator 313 or the patient volume observer 33 to the pressure-regulated volume controller 34 via the adder 302.

The above adders/subtractors, 301-303 and integrators 312-313 may be individually formed individually in the system 30; or alternatively, they can also be integrated into the respective devices. For example, the integrators 312 may be integrated into the patient volume observer 33 and the adder/subtractors 301 and 302 may be integrated as a portion of the patient volume observer 33 and the pressure-regulated volume delivery controller 34, respectively. The adder/subtractor 303 may also be integrated at the output of the pressure-regulated volume delivery controller 34. In addition, the circuit compliance compensated pressure-regulated volume control system 30 may be implemented by individual hardware or a processor integrated into the ventilator 10. The circuit compliance compensated pressure-regulated volume control system 30 may also be implemented by a software executable by a personal or laptop computer connected to the ventilator or by the processor of the ventilator 10 directly.

The above description is given by way of example, and not limitation. Given the above disclosure, one skilled in the art could devise variations that are within the scope and spirit of the invention disclosed herein, including various ways of implementing the circuit compliance compensated volume control systems. Further, the various features of the embodiments disclosed herein can be used alone, or in varying combinations with each other and are not intended to be limited to the specific combination described herein. Thus, the scope of the claims is not to be limited by the illustrated embodiments. 

1. A circuit compliance compensated pressure regulated volume control system in a patient respiratory ventilation system, comprising: a circuit compliance estimator, to provide a relationship between a circuit volume V cc and a differential pressure ΔP_(Y) between a circuit pressure P_(Y) and a positive end expiratory pressure (PEEP) for a patient circuit used in the ventilation system; a circuit volume estimator, operative to estimate a circuit volume VOL_(CKT) _(—) _(EST) distributed to the patient circuit based on the relationship provided by the circuit compliance estimator; a patient volume observer, operative to provide an estimated patient volume VOL_(TID) _(—) _(EST) by subtracting the estimated circuit volume from a measured machine delivered net volume VOL_(NET); and a pressure-regulated volume controller, operative to update a peak airway pressure P_(SET) based on the estimated patient volume VOL_(TID) _(—) _(EST) and a set tidal volume VOL_(TID) _(—) _(SET).
 2. The system of claim 1, wherein the relationship provided by the a circuit compliance estimator includes a linear relationship expressed as V_(CC)=CKT_CMP_(SLP)*(Py−PEEP)+CKT_CMP_(INT) in a V_(CC)−ΔP_(Y) coordinate, where CKT_CPM_(SLP) is a slope of the linear relationship and CKT_CMP_(INT) is an intercept of the linear relationship and a ΔP_(Y) axis.
 3. The system of claim 1, wherein the circuit compliance estimator is operative to measure the differential pressure ΔP_(Y) at various predetermined circuit volumes V_(CC) before the patient is receiving the machine ventilation, so as to estimate the relationship.
 4. The system of claim 1, wherein the measured machine delivered net volume VOL_(NET) is derived by integration of a net flow Q_(NET) defined as a differential flow between a measured inspiratory flow Q_(INSP) and a measure expiratory flow Q_(EXP).
 5. The system of claim 4, further comprising an adder/subtractor for receiving the measured inspiratory and expiratory flows Q_(INSP) and Q_(EXP) to compute the net flow Q_(NET).
 6. The system of claim 5, further comprising an integrator for integrating the flow differential Q_(NET) into the machine delivered net volume VOL_(NET).
 7. The system of claim 1, wherein machine delivered net volume VOL_(NET) is updated with a VOL_(NET) circuit and reset at the start of the every inspiratory phase.
 8. The system of claim 1, wherein: the estimated circuit volume VOL_(CKT) _(—) _(EST) is updated with a VOL_(CKT) _(—) _(EST) circuit, the estimated patient volume VOL_(TID) _(—) _(EST) is updated with a VOL_(TID) _(—) _(EST) circuit; and the measured machine delivered net volume VOL_(NET) is reset with a VOL_(NET)circuit at the start of an expiratory phase following an inspiratory phase during which a net flow Q_(NET) defined as a difference between a measured inspiratory flow Q_(INSP) and a measured expiratory flow Q_(EXP) zero-crossing has been detected.
 9. The system of claim 8, wherein, when the net flow Q_(NET) does not cross zero during the inspiratory phase: the estimated circuit volume VOL_(CKT) _(—) _(EST) is updated with a VOL_(CKT) _(—) _(EST) circuit, the estimated patient volume VOL_(TID) _(—) _(EST) is updated with a VOL_(TID) _(—) _(EST) circuit; and the measured machine delivered net volume VOL_(NET) is reset with a VOL_(NET) circuit when the net flow Q_(NET) crosses zero after the expiratory phase starts or when the expiratory phase has started over a predetermined period of time before the net flow Q_(NET) zero-crossing is detected.
 10. The system of claim 9, wherein the predetermined period of time is about 100 msec.
 11. The system of claim 1, further comprising an adder/subtractor for computing a volume error VOL_(TID) _(—) _(ERR) by subtracting the estimated patient volume VOL_(TID) _(—) _(EST) from the set tidal volume VOL_(TID) _(—) _(SET).
 12. The system of claim 1, wherein the pressure-regulated volume controller further comprises: an error percentage converter providing a volume error percentage VOL_(PCT) _(—) _(ERR) defined as a ratio of an absolute value of a volume error to the set tidal volume VOL_(TID) _(—) _(SET), wherein the volume error VOL_(TID) _(—) _(ERR) is a volume differential between the set tidal volume VOL_(TID) _(—) _(SET) and an estimated patient volume VOL_(TID) _(—) _(EST); a gain scheduler for determining a gain K.sub.PTID; and a pressure integrator for updating a previously computed circuit compliance pressure compensation factor PRS_(TID) _(—) _(CTL) by adding a product BRTH_(PTID) _(—) _(CTL) of the gain K_(PTID) and the volume error VOL_(TID) _(—) _(ERR) thereto at the start of every inspiratory phase.
 13. The system of claim 12, wherein the gain K_(PTID) decreases and increases as the volume error percentage VOL_(PCT) _(—) _(ERR).
 14. The system of claim 12, wherein the circuit compliance pressure compensation factor PRS_(TID) _(—) _(CTL) is initialized with a preset value INI_CKT_PRS in a first breath from which computation of the circuit compliance pressure compensation factor PRS_(TID) _(—) _(CTL) is started.
 15. The system of claim 14, wherein the circuit compliance pressure compensation factor PRS_(TID) _(—) _(CTL) is reset to the preset value INI_CKT_PRS any time when any user preset parameter is changed.
 16. The system of claim 12, wherein the pressure-regulated volume controller further comprises a multiplier for computing the product BRTH_(PTID) _(—) _(CTL) of the gain K_(PTID) and the volume error VOL_(TID) _(—) _(ERR).
 17. The system of claim 16, wherein the pressure-regulated volume controller further comprises a rate limiter for limiting the product BRTH_(PTID) _(—) _(CTL) within an allowable range, such that an amount of pressure correction allowed for each breath is limited within such allowable range.
 18. The system of claim 17, wherein the allowable range includes a maximum value MAX_(PRS) _(—) _(RATE) and a minimum value MIN_(PRS) _(—) _(RATE), and the product BRTH_(PTID) _(—) _(CTL) is limited as: BRTH_(PTID) _(—) _(CTL)=max(KPTID*VOL_(TID) _(—) _(ERR), MIN_(PRS) _(—) _(RATE)) BRTH_(PTID) _(—) _(CTL)=min(BRTH_(PTID) _(—) _(CTL), MAX_(PRS) _(—) _(RATE)).
 19. The system of claim 18, wherein the minimum value MIN_(PRS) _(—) _(RATE) of the product BRTH_(PTID) _(—) _(CTL) is equal to negative maximum value MAX_(PRS) _(—) _(RATE) as MIN_(PRS) _(—) _(RATE)=−MAX _(PRS) _(—) _(RATE).
 20. The system of claim 12, wherein the pressure-regulated volume controller further comprises a pressure restrictor to prevent the circuit compliance pressure compensation factor PRS_(TID) _(—) _(CTL) beyond a range between a predetermined minimum value MIN_(PRS) _(—) _(TID) and a predetermined maximum value MAX_(PRS) _(—) _(TID) from being output.
 21. The system of claim 20, wherein: the predetermined minimum value MIN_(PRS) _(—) _(TID) is equal to negative predetermined maximum value MAX_(PRS) _(—) _(TID) of the circuit compliance pressure compensation factor PRS_(TID) _(—) _(CTL) as: MIN_(PRS) _(—) _(TID)=−MAX_(PRS) _(—) _(TID); and the predetermined value MAX_(PRS) _(—) _(TID) is computed from an average of a user setup maximum and minimum peak airway pressures for the patient as: MAX_(PRS) _(—) _(TID)=(PRS_(MAX)−PRS_(MIN))/2.
 22. The system of claim 12, further comprising a flow sensor operative to measure a patient flow Q_(Y) and an integrator for integrating the measured patient flow Q_(Y) into a measured patient volume VOL_(TID) _(—) _(Y).
 23. The system of claim 22, further comprising a volume limiter operative to freeze an output of the pressure-regulated volume controller at the circuit compliance pressure compensation factor PRS_(TID) _(—) _(CTL) computed in the previous breath when the measured patient volume VOL_(TID) _(—) _(Y) is equal to or larger than the set tidal volume VOL_(TID) _(—) _(SET).
 24. The system of claim 23, wherein the measured machine delivered net volume VOL_(NET) and the measured patient volume VOL_(TID) _(—) _(Y) are reset at the beginning at every inspiratory phase.
 25. The system of claim 22, wherein, when a net flow Q_(NET) defined as a difference between a measured inspiratory flow Q_(INSP) and a measured expiratory flow Q_(EXP) crosses zero during an inspiratory phase, the measured machine delivered net volume VOL_(NET) and the measured patient volume VOL_(TID) _(—) _(Y) are reset at the beginning of an expiratory phase following the inspiratory phase.
 26. The system of claim 25, wherein, when a net flow Q_(NET) has not been detected to cross zero during the inspiratory phase, the measured machine delivered net volume VOL_(NET) and the measured patient volume VOL_(TID) _(—) _(Y) are reset at the time when the net flow Q_(NET) crosses zero after an expiratory phase or at the time the expiratory phase has started over a predetermined period of time before the net flow Q_(NET) crosses zero.
 27. The system of claim 1, further comprising: an integrator for integrating a net flow Q_(NET) into the measured machine delivered net volume VOL_(NET), wherein the net flow Q_(NET) is defined as a flow differential between a measured inspiratory flow Q_(INSP) and a measured expiratory flow Q_(EXP); and a phase detector counting time t_(INSP) into an inspiratory phase and determining a timing when each machine breath is cycling from an inspiratory phase to an expiratory phase.
 28. The system of claim 27, wherein each machine breath is cycling to the expiratory phase when the time entering the inspiratory phase t_(INSP) reaches a predetermined inspiratory time T_(INSP) _(—) _(SET) as: t_(INSP)≧T_(INSP) _(—) _(SET).
 29. A circuit compliance compensated pressure regulated volume control system in a patient respiratory ventilation system, comprising: a patient volume provider operative to provide a measured or estimated patient volume VOL_(TID) _(—) _(Y) or VOL_(TID) _(—) _(EST), wherein the estimated patient volume is computed based on a measured machine delivered net volume VOL_(NET) and a circuit compliance C_(T) of a patient circuit applied to a patient; and a pressure-regulated volume controller, operative to generate a circuit compliance compensation pressure factor PRS_(TID) _(—) _(CTL) for offsetting an airway peak pressure, wherein the circuit compliance compensation pressure factor PRS_(TID) _(—) _(CTL) is generated based on a difference between the patient volume VOL_(TID) _(—) _(Y) or VOL_(TID) _(—) _(EST) and a set tidal volume VOL_(TID) _(—) _(SET).
 30. The system of claim 29, wherein the pressure-regulated volume controller further comprises: a gain scheduler for generating a gain K_(PTID) according to a volume error percentage VOL_(PCT) _(—) _(ERR) which is defined as a ratio between an absolute value of a volume error VOL_(TID) _(—) _(ERR) to the set tidal volume VOL_(TID) _(—) _(SET), where the volume error VOL_(TID) _(—) _(ERR) is defined as a volume differential between the set tidal volume VOL_(TID) _(—) _(SET) and the patient volume VOL_(TID) _(—) _(Y) or VOL_(TID) _(—) _(EST); and a pressure integrator to update the circuit compliance circuit pressure compensation factor PRS_(TID) _(—) _(CTL) by adding a product of the gain K_(PTID) and the volume error VOL_(TID) _(—) _(ERR) thereon.
 31. The system of claim 30, wherein the gain scheduler is operative to adjust magnitude of the gain K_(PTID) according to the volume error percentage VOL_(PCT) _(—) _(ERR).
 32. The system of claim 30, further comprising a multiplier for computing the product of the gain K_(PTID) and the volume error VOL_(TID) _(—) _(ERR).
 33. The system of claim 30, further comprising a pressure correction limiter for limiting the product of the gain K_(PTID) and the volume error VOL_(TID) _(—) _(ERR) within a predetermined range.
 34. The system of claim 30, further comprising an adder to add the circuit compliance pressure compensation factor PRS_(TID) _(—) _(CTL) to an initial set peak airway pressure P_(SET) _(—) _(INI) defined as: P_(SET) _(—) _(INI)=(PRS_(MAX)+PRS_(MIN))/2.
 35. The system of claim 29, wherein the pressure-regulated volume controller further comprises a pressure restrictor from restricting the circuit compliance pressure compensation factor PRS_(TID) _(—) _(CTL) beyond a range between a predetermined minimum value MIN_(PRS) _(—) _(TID) and a pre-determined maximum value MAX_(PRS) _(—) _(TID) from being output.
 36. The system of claim 29, wherein the patient volume provider includes either a volume integrator for integrating a patient flow Q_(y) into the measured patient volume VOL_(TID) _(—) _(Y) or a patient volume estimator for computing the estimated patient volume VOL_(TID) _(—) _(EST).
 37. A method for circuit compliance compensated pressure regulated volume control in a patient respiratory ventilation system, comprising: a) measuring a patient volume VOL_(TID) _(—) _(Y) with a VOL_(TID) _(—) _(Y) circuit through a flow sensor installed at a patient piece of a patient circuit in the ventilation system, or estimating a patient volume VOL_(TID) _(—) _(EST) with a VOL_(TID) _(—) _(EST) circuit based on a machine delivered net volume VOL_(NET) and a circuit compliance C_(T) of the patient circuit; and b) predetermining, an initial value INC_CKT _PRS for a circuit compliance pressure compensation factor PRS_(TID) _(—) _(CTL) and updating the circuit compliance pressure compensating factor PRS_(TID) _(—) _(CTL) based on a set tidal volume VOL_(TID) _(—) _(SET) and the patient volume VOL_(TID) _(—) _(Y) or VOL_(TID) _(—) _(EST) for each breath.
 38. The method of claim 37, further comprising: c) initializing the circuit compliance pressure compensation factor PR_(STID) _(—) _(CTL) to the initial value INI_CKT _PRS when any user setup parameter of the ventilation system is changed.
 39. The method of claim 37, further comprising a step of resetting and updating the measured patient volume VOL_(TID) _(—) _(Y) and the measured machine delivered net volume VOL_(NET) at the beginning of every inspiratory phase with respective VOL_(TID) _(—) _(Y) and VOL_(NET) circuits.
 40. The method of claim 39, wherein, when the estimated patient volume VOL_(TID) _(—) _(EST) is selected for generating the circuit compliance pressure compensation factor PRS_(TID) _(—) _(CTL), step (a) further comprises: a1) providing a machine delivered net flow Q_(NET) computing a flow differential of a measured inspiratory flow Q_(INSP) and a measured expiratory flows Q_(EXP); and a2) integrating the machine delivery net flow Q_(NET) into the machine delivered net volume VOL_(NET).
 41. The method of claim 40, wherein step (a) further comprises: a3) deriving a relationship between circuit pressure P_(Y) and circuit volume V_(CC) from the circuit compliance C_(T); a4) estimating a circuit volume VOL_(CKT) _(—) _(EST) from the relationship by providing a measured patient circuit P.sub.Y; and a5) subtracting the estimated circuit volume VOL_(CKT) _(—) _(EST) from the measured machine delivered net volume VOL_(NET) to obtain the estimated patient volume VOL_(TID) _(—) _(EST).
 42. The method of claim 41, wherein, when the net flow Q_(NET) is detected to cross zero during an inspiratory phase, at the start of an expiratory phase following the inspiratory phase, the estimated circuit volume VOL_(CKT) _(—) _(EST) is updated with a VOL_(CKT) _(—) _(EST) circuit, the estimated patient volume VOL_(TID) _(—) _(EST) is updated with a VOL_(TID) _(—) _(EST) circuit; and the measured machine delivered net volume VOL_(NET) is reset.
 43. The method of claim 41, wherein, when the net flow QNET does not cross zero during an inspiratory phase, the estimated circuit volume VOL_(CKT) _(—) _(EST) is updated with a VOL_(CKT) _(—) _(EST) circuit, the estimated patient volume VOL_(TID) _(—) _(EST) is updated with a VOL_(TID) _(—) _(EST) circuit; and the measured machine delivered net volume VOL_(NET) is reset at the earlier when the net flow Q_(NET) crosses zero during the expiratory phase starts or when the expiratory phase has started over a predetermined period of time before the net flow Q_(NET) has crossed zero.
 44. The method of claim 39, wherein step (b2) further comprises multiplying the gain K_(PTID) with the volume error VOL_(TID) _(—) _(ERR) to obtain the pressure correction.
 45. The method of claim 44, wherein step (b2) further comprises limiting the pressure correction between a predetermined maximum value and a predetermined minimum value.
 46. The method of claim 37, wherein step (b) further comprises: b1) computing a volume error percentage VOL_(PCT) _(—) _(ERR) defined as a ratio of an absolute value of a volume error VOL_(TID) _(—) _(ERR) to the set tidal volume VOL_(TID) _(—) _(SET), wherein the volume error VOL_(TID) _(—) _(ERR) is a volume differential between the set tidal volume VOL_(TID) _(—) _(SET) and the patient volume VOL_(TID) _(—) _(Y) or VOL_(TID) _(—) _(EST); b2) determining a gain K_(PTID) as a function of the volume error percentage VOL_(PCT) _(—) _(ERR), so as convert the volume error VOL_(TID) _(—) _(ERR) into a pressure correction for the circuit compliance compensation factor PRS_(TID) _(—) _(CTL); and b3) updating the circuit compliance pressure compensation factor PRS_(TID) _(—CTL) by adding the pressure correction thereto.
 47. The method of claim 46, wherein step (b) further comprises b4) limiting the updated circuit compliance pressure compensation factor between a predetermined allowable range.
 48. The method of claim 46, further comprising the step of: d) providing a set peak airway pressure P_(SET) by adding the updated circuit compliance pressure compensation factor PRS_(TID) _(—) _(CTL) to an initial set peak airway pressure as: P_(SET)=PRS_(TID) _(—) _(CTL)+P_(SET) _(—) _(INI). 